Creation of curved cuts in the inside of the eye cornea

ABSTRACT

A device for isolating a lenticle in the cornea of an eye. The device includes: a laser beam source to emit pulsed laser radiation having a pulse frequency of 1.2 MHz to 10 MHz, a pulse energy of 1 nJ to 200 nJ and a wavelength penetrating the cornea; a beam-forming unit having beam optics with an image field and that bundles pulsed laser radiation into a focus located inside the image field, and which has a maximum diameter of less than 3 μm; a beam-deflection unit shifting the focus in the cornea and inside the image field, the focus moving along a path when the image field is resting; and a control unit to control the source and the beam-forming unit to isolate the lenticle by specifying the path. The lenticle is delimited by a cut surface which is curved with regard to a front surface of the cornea.

PRIORITY CLAIM

The present application is a continuation of U.S. patent applicationSer. No. 14/774,677, filed Sep. 10, 2015, which is a National Phaseentry of PCT Application No. PCT/EP2014/052167, filed Feb. 4, 2014,which claims priority from German Patent Application Number102013204496.8, filed Mar. 14, 2013, the disclosures of which are herebyincorporated by reference herein in their entirety.

FIELD OF THE INVENTION

The invention relates to a device for isolating a lenticle in the corneaof an eye, which device has a laser beam source which is designed toemit pulsed laser radiation with a wavelength which penetrates into thecornea, a beam forming unit which has beam optics which bundle thepulsed laser radiation in the cornea into a focus, and a beam deflectionunit, which shifts a focus of the radiation in the cornea, wherein acontrol unit is provided which is designed to control the laser beamsource and the beam forming unit, in order to isolate the lenticle inthe cornea, which lenticle is delimited by a cut surface.

The invention also relates to a method for isolating a lenticle in thecornea of an eye, wherein at least one cut surface is established in thecornea, which surface defines the lenticle and the cut surface in thecornea is created by emitting pulsed laser radiation, wherein pulsedlaser radiation which has a wavelength which penetrates into the corneais used, and a focus of the laser radiation is shifted in the cornea.

BACKGROUND OF THE INVENTION

The shape of the front surface of the cornea of an eye is important forthe imaging properties of the eye. Therefore, it has long been known touse the cornea of an eye to correct impaired vision, with the aim ofmodifying the front surface of the cornea of an eye and thus itsrefractive properties and in this way compensate for impaired vision. Inthe state of the art, surgical procedures which loosen a lamella in thecornea of an eye, fold this lamella back and then remove material fromthe inside of the cornea of an eye which has been exposed as a result,have been developed for this purpose. Subsequently, the lamella isfolded back into place, leaving the cornea of an eye with a differentlyshaped front surface, due to the removal of material. In the state ofthe art, this correction method is abbreviated inter alia to LASIK;hereinafter it will be identified as lamella-releasing correction ofimpaired vision. In earlier embodiments, the lamella was loosened bymeans of a mechanical keratome. The cornea of an eye was pushed flat bya flat contact lens and the lamella cut by means of the mechanicalkeratome. In a development, so-called laser keratomes have started to beused by now. Inter alia a laser keratome from Ziemer Ophthalmic SystemsAG, Port, Switzerland, is known for this purpose. With regard to itsbeam deflection, it was designed to create the lamella to be foldedback. A further laser keratome was developed by Intralase Inc., USA,which by now is owned by Abbott Laboratories, Illinois, USA. Both laserkeratomes work by means of pulsed laser radiation, wherein repetitionrates and pulse energies differ.

Surgical correction of impaired vision has been further developed tomethods which isolate and extract material in the cornea. The materialusually has the form of a lenticle, which is why these methods arecalled lenticle-extracting methods or devices here. Also, for reasons ofclarity, the volume to be isolated and extracted is identified as a“lenticle”, even if in specific applications a non-lenticle-shapedvolume is to be isolated and extracted.

The devices and methods named at the outset relate to the method oflenticle extraction. Lenticle-extracting devices and methods have theadvantage that the front surface of the cornea is damaged in a very muchsmaller area. It is no longer necessary to have an almost completelyannular incision into the front surface of the cornea, as is requiredfor releasing a lamella which would expose the inside of the cornea.Instead, a smaller incision at the edge, which leads to the isolatedvolume, and through which the isolated volume can be removed, is enough,optionally after reduction of the isolated material. The method oflenticle extraction requires that the cut surfaces isolating thelenticle be created with high precision in the inside of the cornea. Inorder to correct impaired vision, so as to use as little tissue aspossible, additionally at least one of the cut surfaces delimiting thelenticle should lie at a non-uniform distance from the front surface ofthe cornea. Also here there is a difference from the approach whichloosens and folds back a lamella of the cornea, as there the onlylamella-creating cut surface may lie at a uniform distance from thefront surface of the cornea, thus parallel to the front surface of thecornea. If the front surface of the cornea is pressed flat with a flatcontact lens, when creating the cut in the lamella, only one cutsurface, which lies parallel to the surface of the contact lens as faras the edge sections, and for its part is also flat, needs to becreated.

Lenticle-extracting correction of impaired vision is basically describedin WO 2004/105660 and WO 2004/105661. Additionally, developments areknown in the state of the art. Thus WO 2005/011547 discloses the use ofcontour lines for rapid isolation of lenticles, while WO 2008/055697indicates calculation rules for how the boundary surfaces of thelenticle, i.e., the cut surfaces being created, can be chosen. It isknown in particular from this document to divide the cut surfacesdelimiting the lenticle into an anterior flap surface which is at auniform distance from the front surface of the cornea of an eye and aposterior lenticle surface which is not at a uniform distance from thefront surface of the cornea. The distance between the surfaces, and thustheir shape, influences the curvature of the cornea after correction.

WO 2008/055705 and WO 2008/055706 deal with the issue of curvature ofthe image field when using a non-planar contact lens and creatingcontrol data for the surgical procedure.

The cut surface is usually created by pulsed laser radiation. For this,the targets of the laser radiation are arranged along a path which liesin the cut surface and ultimately specifies the cut surface. WO2008/055698 outlines the arrangement of targets along the path, whereinit is provided not to specify a target for every pulse of laserradiation emitted into the cornea of an eye.

WO 2008/131878 discusses the question of how, if laser surgery isinterrupted, further treatment can take place which takes intoconsideration changes to the tissue of the cornea which have alreadybeen created.

WO 2009/059711 and WO 2009/059730 deal with different profiles of thelenticle to be removed for specific corrections of impaired vision,specifically correcting hyperopia, and specify minimum values for thelenticle.

WO 2003/059563 discloses operating parameters for a laser device foroperations to correct impaired vision by means of lenticle extraction.The same applies to EP 1628606 B 1.

In the state of the art, the femtosecond laser keratome VisuMax fromCarl Zeiss Meditec AG is known for the lenticle-extracting method. Ituses a femtosecond fibre laser which emits in the infrared spectralrange and which emits at a pulse repetition rate of 500 kHz laser pulseswhich are focussed in the cornea of an eye.

The time it takes to create a cut surface is of great importance bothfor the quality of the correction of impaired vision and also foracceptance by patients. The longer the duration of the intervention, thegreater the risk of disruptive eye movements which reduce the precisionof the creation of the cut surface or can even lead to it no longerbeing possible to create any coherent cut surfaces, and the procedureneeding to be interrupted. Also, a longer-lasting intervention placesunwanted stress on the patient.

With lamella-releasing correction of impaired vision, the quality of theoptical correction is determined essentially by the precision of thevolume removed after releasing the lamella. The position of thelamella-releasing cut surface itself is of less, or even no, importance.On the contrary, the exact positioning of the cut surfaces in the corneaof an eye is of great importance for the quality of the result of alenticle-extracting correction of vision. As the cut surface is createdby adjusting the focus of the pulsed laser radiation along a path,ultimately the positioning accuracy of the focus in the cornea of an eyeis important. Here, it must not be forgotten that this is a livingtissue, which can occasionally be modified during intervention and alsodoes not necessarily react in linear fashion to changes in parameters.

SUMMARY OF THE INVENTION

Therefore, the object of the invention is to develop a device of thetype named at the outset or a method of the type named at the outsidesuch that a quick creation of a cut surface with simultaneously highprecision can thus be achieved.

This object is achieved, according to the invention, by a device forisolating a lenticle in the cornea of an eye, which has:

a laser beam source that is designed to emit pulsed laser radiation with

-   -   a pulse frequency of 1.2 MHz to 10 MHz,        -   a pulse energy of 1 nJ to 200 nJ, and        -   a wavelength which penetrates into the cornea;    -   a beam forming unit which has        -   beam optics, which have an image field and which bundle the            pulsed laser radiation in the cornea into a focus which is            located inside the image field and which has a maximum            diameter of less than 3 μm, and        -   a beam deflection unit which shifts the focus in the cornea            and inside the image field, wherein the focus moves along a            path while the image field is resting; and

a control unit, which is designed to control the laser beam source andthe beam forming unit, in order to isolate the lenticle in the cornea byspecifying the path, which lenticle is delimited by at least one cutsurface which is curved with regard to a front surface of the cornea.

The object is further achieved by a method for isolating a lenticle inthe cornea of an eye, wherein

at least one cut surface is established in the cornea, which surfacedefines the lenticle and is curved with regard to a front surface of thecornea;

-   -   a path which lies in the cut surface is established;    -   there is emitted into the cornea pulsed laser radiation with        -   a pulse frequency of 1.2 MHz to 10 MHz,        -   a pulse energy of 1 nJ to 200 nJ, and        -   a wavelength which penetrates into the cornea;    -   beam optics are used, which optics have an image field and which        bundle the pulsed laser radiation in the cornea into a focus        which is located inside the image field and which has a maximum        diameter of less than 3 μm; and    -   the focus in the cornea and inside the image field is shifted,        wherein the focus moves along a path while the image field is        resting.

The invention combines different features which together make possiblethe creation of a cut surface which is curved with regard to the frontsurface of the cornea. It is not thus a conventional lamella-releasingcut surface, but a cut surface which has no uniform distance from thefront surface of the cornea in relation to a cut plane through the eyewhich contains the axis of vision or the optical axis of the eye. Withregard to the front surface of the cornea of the eye the inventionprovides the curvature, more precisely a two-dimensional curvature, toexist in a central area about the optical axis or the axis of vision ofthe eye which area for example has a diameter of not more than 10 mm.This is the area which is essential for optical correction, and in thisarea, customary initial laser cuts of lamella-releasing correctionmethods have a uniform distance between the front surface of the corneaof an eye and the cut surface, which causes the lamella to expose theinside of the cornea of an eye.

For the following reasons, the combination according to the inventiongoes beyond a simple aggregation of features and achieves a combinedeffect:

The individual laser pulses which form the cut surface along the pathact differently in the cornea of an eye, depending on pulse energy,pulse frequency and focus diameter. With regard to the separation oftissue due to pulsed laser radiation, two different ways of working canbe identified. These different processes will be called “tissuesplitting” and “tissue cutting” hereinafter.

If laser pulses are focussed into the cornea under specific conditions,in the focal volume there is tissue dissolution which releases gaseswhich are at high pressure and thus exert mechanical forces on the areasurrounding the tissue. The corneal tissue consists of a lamellarcollagen structure, with the result that, to the best of the inventor'sknowledge, the mechanical forces create microruptures which travel alongthe lamellae. Thus, in addition to the primary process of tissuedissolution in the focal volume, there is a secondary effect which leadsto tissue splitting along the collagen structure. If, on the other hand,comparatively small pulse energies and higher repetition rates are beingused, there is no secondary effect of tissue splitting, but merely thetissue dissolution created in the volume of the focus causes theseparation. The corneal tissue is thus cut, largely regardless of thecollagen structure.

The inventors recognized that there is no abrupt transition betweentissue splitting and tissue cutting. In the parameter space of the laserpulse application there is a transition region in which either onemechanism or the other plays a more or less substantial role in theprocess of tissue separation. Furthermore, it has been shown that inlenticle-extraction methods and devices thus far in clinical practiceexclusively utilize parameter sets which led to the secondary effect oftissue splitting having a substantial role to play in the separationprocess. Exclusively tissue-cutting sets of parameters are currentlyused in clinical practice only by the laser keratome of ZiemerOphthalmic Systems AG, Port, Switzerland. However, to the best of publicknowledge, this device is not capable of creating cut surfaces which arecurved with regard to the front surface of the cornea, and, as alreadystated at the outset, such way of working does not offer any substantialadvantage for applications using the lamella-releasing method, and istherefore not important.

It should be emphasised that different ways of working, i.e., theinfluence of parameters on the question of whether tissue splitting ortissue cutting prevails when creating lenticles, have been identifiedfor the first time by the inventors. The difference between the ways ofworking with this method is not mentioned in the state of the art. Also,the literature does not assign the individual realisations of the stateof the art to these ways of working.

From their work, the inventors recognized also that, with regard to theprecision to be achieved, there is a substantial difference betweentissue splitting on the one hand, and tissue cutting on the other, onlyif curved cuts are made. This is because tissue splitting generallyalways proceeds along the lamellae of the collagen structure of thecorneal tissue. With lamellar cuts there is therefore no advantage ordisadvantage between lamellar splitting and lamellar cutting in themachining result. For curved cut surfaces it is different: This isbecause it is not possible, because of the physiologically givenlamellae thickness and structure, to place a curved cut surface withhigh contour accuracy at just any point in the cornea of an eye iftissue-splitting separation is taking place.

The mechanism of tissue cutting allows a very much more precise cutsurface positioning and in particular a higher contour accuracy to beachieved. The inventors trace this back to the fact that, in atissue-cutting process other than tissue splitting, the cut surface doesnot necessarily follows in boundary surfaces between lamellae of thecollagen structure of the corneal tissue, but also can be arrangedwithin a lamella. An advancing fissure (advancing the splitting beforethe proceeding sequence of laser pulses) which would occur in thelamella plane during tissue splitting is prevented and the separationtakes place precisely in the focus position. However, tissue splittingcan also be understood as a sort of digitisation of the cut surfaceposition, wherein the smallest unit is the thickness of the lamella as atissue-splitting created cut surface tends always to lie in boundarysurfaces between individual lamellae of the corneal tissue. This is nota defect for cuts which are effected at a uniform distance from thefront side of the cornea, because the lamella structure follows thefront side of the cornea with good accuracy. For curved cut surfaces ofthe lenticle, the distance of which from the front side of the corneavaries depending on radius and optionally angle, this type of creationof a cut surface proves disadvantageous.

With regard to pulse frequency, pulse energy and focus diameter, theserelationships lead, particularly reliably, to the parameter rangeaccording to the invention having a tissue separation in which theprocess of tissue cutting strongly prevails. The combination with thecreation of a cut surface which is curved with regard to the frontsurface of the cornea and thus does not necessarily follow the boundarysurface between lamellae of the collagen structure of the corneal tissue(which otherwise travels largely parallel to the front surface of thecornea) therefore leads to a particularly accurate cut surfacepositioning and high contour accuracy. In the working range according tothe invention, the contribution of tissue splitting is reduced in favorof the effect of tissue cutting, and therefore the cut surface and thusthe isolation of the lenticle follow the specified values more preciselyfor lenticle extraction.

The tissue cutting effect is particularly great if the pulse energy isless than 100 nJ and, particularly preferably, less than 10 nJ. A pulseenergy range of 10 nJ to 80 nJ has proved particularly favorable. Thesame applies for the pulse length of the pulsed laser radiation which,at infrared wavelengths, should be no more than 1 ps.

The wavelength of the laser radiation used is such that the laserradiation can penetrate into the cornea of an eye (transmissionfactor≥0.8) and there leads to tissue separation in the inside of thecornea, by means of non-linear effects. For this, a wavelength of1030-1060 nm has proven useful. Alternatively, laser radiation in theultraviolet spectral range between 300 nm and 400 nm can be used. Itactually tends towards a higher linear interaction fraction (absorption)than the named infrared radiation, but is likewise suitable if the focusdiameter does not exceed 2 μm and the pulse frequency is not more than 2MHz. If laser pulses from this ultraviolet wavelength range are used,pulse lengths of a few ns can also be used effectively.

The lenticle is isolated by the focus being shifted within the imagefield of the beam optics used and the image field being resting withregard to the cornea to be machined. This is where it differs from thelaser keratome of Ziemer Ophthalmic Systems AG, in which a microscopeobject is used, the image field of which is much too small to achievecomplete detection of the area in the cornea to be machined. Themicroscope object and thus the image field is therefore shifted withthis laser keratome. A curved cut surface thus cannot be created withjustifiable expense, which is why this laser keratome pushes the frontsurface of the cornea of an eye flat by means of a planar contact lens,and therefore the created cut surface automatically lies parallel to thefront surface of the cornea of an eye. However, the invention uses anresting image field, for which, with regard to the area to be machined,a diameter of at least 3 mm, preferably at least 6 mm and particularlypreferably at least 7 mm, is sensible. Small image fields hinder thecreation of cut surfaces or are too small for customary lenticles to beisolated.

As the surface is cut by shifting the focus within the image field alonga path which lies in the cut surface, almost any curved cut surface inthe cornea of an eye can be created with a suitable three-dimensionaladjustment of the focal position. Therefore, it is no longer necessaryto flatten the cornea of an eye. Instead, work can be done on a curvedcontact lens, wherein it is preferable that a contact surface of thiscontact lens to be placed on the front surface of the cornea has aradius of curvature of not more than 50 mm, preferably not more than 20mm. The curvature of the contact surface of the contact lens specifiesthe curvature of the cornea during intervention.

To create the curved cut surface, it is also advantageous if the beamoptics have an objective with a numerical aperture of at least 0.33 inthe cornea.

It is understood that the features mentioned above and those yet to beexplained in the following are applicable, not only in the statedcombinations, but also in other combinations or singly, withoutdeparture from the scope of the present invention.

In particular, the invention can advantageously be used in slightlymodified form also for the creation of curved cuts in other elements ofthe eye, for example in the lens or the vitreous body.

BRIEF DESCRIPTION OF THE FIGURES

The invention is explained by way of example in yet greater detail inthe following with reference to the attached drawings, which alsodisclose features essential to the invention. There are shown in:

FIG. 1 a schematic representation of a device for carrying out alenticle-extraction correction of impaired vision,

FIG. 2 a simplified sectional representation through the cornea of aneye to illustrate the lenticle to be isolated and extracted, and

FIG. 3 a projection of a cut surface delimiting the lenticle, toillustrate the creation of the cut surface.

DETAILED DESCRIPTION

FIG. 1 shows, schematically, a device 1 for carrying out alenticle-extracting correction of impaired vision. Device 1 has a laser2 which provides pulsed laser radiation, wherein in the embodimentoutlined, the laser 2 emits a pulsed pure beam 3 which has a wavelengthwhich penetrates into the tissue of the cornea of an eye, with theresult that a machining by means of non-linear effects can take placethere. Pure beam 3 is shaped by a chopper 4 with regard to pulseduration, wherein predistortion known from the state of the art can takeplace, which ensures that the desired pulse length of for example ≤1 psis present after passing through the further optical path of the beampath in the material, i.e., in the cornea of an eye. Chopper 4 and laser2 form a laser beam source 5 which emits a pulsed laser beam 6 of thedesired pulse length.

Pulsed laser beam 6 also passes through a scanner 7 which preferablybrings about a two-dimensional deflection transverse to the direction ofpropagation of the laser radiation. The laser beam 6 scanned in this wayis focussed into the cornea of an eye by an objective 8. Scanner 7 formsa beam forming unit 9 together with the objective 8, which ensures thatpulsed laser radiation 6 is focussed into a cornea of an eye inlocations which can be set, wherein the focus diameter there is lessthan 3 μm.

Laser beam source 5 can optionally comprise a so-called pulse pickerwhich can for example be part of the chopper 4. This pulse pickerchanges the frequency of the laser radiation pulses in the pure beam 3,which pulses have a machining effect on the cornea of an eye. Thus forexample it is possible to design the laser 2 such that it provides apure beam 3 with a pulse frequency which is clearly higher than thatpulse frequency which is desired for the machining-effective laserpulses of the laser beam 6. Then, the pulse picker reduces the frequencyof the effective laser radiation pulses by rendering the machiningeffect of individual laser radiation pulses harmless. This can forexample take place by the pulse picker increasing the pulse length. Theimportance of the pulse picker known in the state of the art will beexplained later on with the help of FIG. 3.

In the embodiment shown in FIG. 1, the pulse frequency of the pulsedlaser beam 6 is between 1.2 MHz and 10 MHz, wherein the frequency isrelative to those pulses which have a machining effect, i.e., pulseswhich are not rendered harmless by a pulse picker if present.

The energy of these pulses of the pulsed laser beam 6 is between 1 nJand 200 nJ, preferably between 10 nJ and 100 nJ, particularly preferablybetween 20 nJ and 80 nJ.

The wavelength of laser beam 6 lies in a range of 1030 nm to 1060 nm or300 nm to 400 nm or another spectral range which can penetrate into thecornea, for which the cornea thus has a transmission factor of at least0.8.

Device 1 also comprises a contact lens 10 which serves to fix the eye 11and also to give the front surface of the cornea 12 of an eye 11 adesired and known shape. The corresponding contact surface of contactlens 10 has a radius of curvature of 50 mm or less, particularlypreferably 20 mm or less, for this purpose.

Objective 8 bundles the laser radiation 6 into a focus 13 which isinside the cornea 12. Focus 13 has a maximum diameter of 3 μm,preferably a maximum of 2 μm. The maximum diameter is the largestdiameter which, e.g., in the event of an elliptical focus spot, ismeasured along the large semiaxis. In the event of a circular spot, thespot diameter is the relevant measurement.

The dotted line of FIG. 1 shows that, depending on the effect of thescanner 7, the focus 13 is at different points in the cornea 12 of aneye 11. In the design of FIG. 1, the scanner 7 brings about a deflectiontransverse to the main direction of incidence of the laser radiation 6.The focus position is adjusted along the main direction of incidence bysuitable actuation of the objective 8, which is designed to be suited toa z-adjustment.

The laser beam source 5 (in the design of FIG. 1 produced by laser 2 andchopper 4) as well as the beam forming unit 9 (in the design of FIG. 1produced by scanner 7 and objective 8) are connected to a controlapparatus 14 via control lines, not shown in more detail, which controlapparatus controls these elements in suitable manner. The actuating ofthe control apparatus 14 creates a cut surface in the cornea of an eye.The corresponding relationships are represented in a sectionalrepresentation in FIG. 2, which shows the cornea 12 schematically.

A lenticle 15 in the cornea 12 is isolated by adjusting the focus 13 ofthe pulsed laser radiation 6. Lenticle 15 is delimited at the front by aflap surface 16 and at the back by a lenticle surface 17. In order to beable to keep the boundary surfaces of the lenticle 15 as simple aspossible, the flap surface 16 is at a uniform distance from the frontsurface 18 of cornea 12. Flap surface 16 is thus not curved with regardto front surface 18. This is different in lenticle surface 17 which iscurved with regard to the front surface 18. Without such a curvature,the removal of the lenticle 15 would not change the curvature of thefront surface 18 of the cornea 12. If the lenticle 15 is removed,however, the lenticle surface 17, curved with regard to front surface18, changes the curvature of the front surface 18 of the cornea 12. Thisis removed by a lateral cut, not shown in FIG. 2, which cut for exampleleads at the edge of lenticle 15 from the flap surface 16 to the frontsurface 18 and makes it possible for the isolated lenticle 15 to beextracted, optionally after reduction of the material of the lenticle15. In the representation of FIG. 2, flap surface 16 and lenticlesurface 17 are symmetrical to the optical axis OA. This is setautomatically for flap surface 16 if it has a uniform distance fromfront surface 18.

The boundary surfaces of the lenticle 15 may naturally also comprisefurther surfaces apart from flap surface 16 and lenticle surface 17. Forexample, with a lenticle 15 which is thinner on the optical axis OA thanin regions far away from the axis, an additional edge surface can beprovided which connects flap surface 16 to lenticle surface 17, whichthen has a more curved path than flap surface 16 and front surface 18.

The cut surfaces for isolating the lenticle 15 are thereby created bythe focus 13 being shifted along a path which lies in the correspondingsurface. This is shown by way of example in FIG. 3 with the help oflenticle surface 17 which, for reasons of clarity, is elliptical here.This is intended to show that device 1 can be used to correct not only aspherical visual defect but also an astigmatism. Basically, duringhigher-aberration corrections, lenticle 15 is no longerrotation-symmetrical to the optical axis OA. FIG. 3 shows a folding-upof the lenticle surface 17 in the drawing plane. In FIG. 3, a path 19 isdrawn in using a dotted line. The position of the focus 13 is adjustedalong this path. Generally, naturally not just one adjustment transverseto the optical axis OA is necessary, but also an adjustment of the focusposition along the optical axis OA. This therefore cannot be seen inFIG. 3, as this figure shows a folding-up of the lenticle surface 17 inthe drawing plane, which is why, in the representation of FIG. 3, path19 lies in a plane. By looking at the cut through lenticle 15 in FIG. 2it becomes clear that, the greater the distance from the optical axisOA, the further away from the front surface 18 the z-position of thefocus is shifted.

Targets 20 are drawn in along the path 19 of FIG. 3. In each case theyindicate a point at which a laser pulse of the pulsed laser radiation 6is emitted. The lenticle surface 17 is designed as a cut surface overallby arranging the targets 20 in series along the path 19 and by asuitable choice of the path 19. The distances between targets 20 arechosen such that the fewest possible material bridges remain, meaningthat the lenticle surface 17 is thus generated entirely as a cutsurface.

With the help of FIG. 3 it can easily be understood why it isadvantageous to make it possible to change the pulse frequency of thepulsed laser beam 6. If it were desired to arrange the targets 20 to beas equidistant as possible, the pulse frequency and the shift speed ofthe beam forming unit 9 can be adapted to one another. As a high pulsefrequency laser 2 can generally be adjusted only at great expense, it isadvantageous to provide firstly a pure beam 3 with the laser 2, whichpure beam has a pulse frequency which is greater than or equal to themaximum pulse frequency desired for the laser beam 6. It may be easierto produce such a laser 2 and to combine same with a pulse picker thanto design a laser with a pulse frequency which can be directly adjusted.Thus the pulse frequency can be adapted to the shift speed, and the timetaken to create cut surfaces is reduced.

The parameters for pulse energy, pulse frequency, focus diameter andoptionally pulse length, named in the description of the figures as wellas in the general part of the description, lead to the cut surfacesbeing created with a mechanism for separating tissue which uses tissuecutting and essentially tissue splitting to their full capacity. Thus adesired position for the delimiting cut surfaces of the lenticle 15 canbe produced with great precision.

What is claimed is:
 1. A device for generating a cut in the interior ofan eye, the device comprising: a laser beam source that is designed toemit a raw train of laser radiation pulses having a raw pulse frequencyof at least 1.2 MHz and a wavelength which penetrates a cornea of theeye, wherein each laser radiation pulse of the raw train is adapted toseparate layers of material within the eye; a pulse picker which selectssome laser radiation pulses of the raw train to provide a modified trainof laser radiation pulses adapted to separate layers of material withinthe eye, the modified train having a pulse frequency reduced over theraw pulse frequency; beam optics which bundle the laser radiation pulsesinto a focus located in the eye, and a beam scanner which shifts thefocus in the eye along a path to generate the cut by the modified trainof laser radiation pulses emitted while the focus is shifted along thepath; and a processor, which is connected with the beam scanner and thepulse picker and is designed to control the beam scanner by specifyingthe path and thus defining location and extension of the cut.
 2. Thedevice according to claim 1, wherein the raw pulse frequency is not morethan 10 MHz.
 3. The device according to claim 1, wherein the laser beamsource is designed to emit the laser radiation pulses having a pulseenergy of 1 nJ to 200 nJ, in particular not more than 100 nJ.
 4. Thedevice according to claim 1, wherein the laser beam source is designedto emit the laser radiation pulses having a pulse energy of 10 nJ ormore.
 5. The device according to claim 1, wherein the laser beam sourceis designed to emit the laser radiation pulses having a wavelength of1030 nm to 1060 nm.
 6. The device according to claim 1, wherein thelaser beam source is designed to emit the laser radiation pulses havinga wavelength of 300 nm to 400 nm.
 7. The device according to claim 6,wherein the laser beam source is designed to emit the laser radiationpulses having a pulse length of less than 1 ps.
 8. The device accordingto claim 1, wherein the focus has a maximum diameter of less than orequal to 3 μm, in particular less than or equal to 2 μm.
 9. The deviceaccording to claim 1, further comprising a contact lens comprising acontact surface for placing on the cornea, wherein the contact surfaceis concavely curved, in particular has a radius of curvature of not morethan 50 mm, preferably not more than 20 mm.
 10. The device according toclaim 1, wherein the beam optics comprise an objective with a numericalaperture of at least 0.33.
 11. The device according to claim 1, whereinthe beam optics comprise an optical field with a diameter of ≥3 mm, inparticular of ≥6 mm and particularly preferably of ≥7 mm.
 12. The deviceaccording to claim 1, wherein the beam optics comprise an optical fieldand the beam scanner shifts the focus within the optical field while theoptical field is resting in the eye.
 13. A method device for generatinga cut in the interior of an eye, the method comprising: emitting a rawtrain of laser radiation pulses having a raw pulse frequency of at least1.2 MHz and a wavelength which penetrates a cornea of the eye, whereineach laser radiation pulse of the raw train is adapted to separatelayers of material within the eye; selecting some laser radiation pulsesof the raw train to provide a modified train of laser radiation pulsesadapted to separate layers of material within the eye, the modifiedtrain having a pulse frequency reduced over the raw pulse frequency;focussing the laser radiation pulses into a focus located in the eye,and shifting the focus in the eye along a path to generate the cut bythe modified train of laser radiation pulses emitted while the focus isshifted along the path, wherein the path defines location and extensionof the cut.
 14. The method according to claim 13, wherein the raw pulsefrequency is not more than 10 MHz.
 15. The method according to claim 13,wherein the laser radiation pulses have a pulse energy of 1 nJ to 200nJ, in particular not more than 100 nJ.
 16. The method according toclaim 13, wherein the laser radiation pulses have a pulse energy of 10nJ to 80 nJ.
 17. The method according to claim 13, wherein thewavelength is between 1030 nm to 1060 nm or between 300 nm to 400 nm.18. The method according to claim 13, wherein the laser radiation pulseshave a pulse length of less than 1 ps.
 19. The method according to claim13, wherein the maximum diameter is less than or equal to 2 μm.
 20. Themethod according to claim 13, further comprising the steps of providinga contact lens comprising a contact surface and placing the contactsurface onto the cornea, wherein the contact surface is concavelycurved, in particular has a radius of curvature of not more than 50 mm,preferably not more than 20 mm.